JP2010164881A - Cassette for radiographing radiation image - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a cassette for radiographing radiation images, protecting a built-in member from breakage caused by impact or the like and interchangeably usable for a radiographic device (Bucky) for a CR (computed radiography) cassette, and for an FPD (flat panel detector) system. <P>SOLUTION: The radiographic cassette for radiation images has: a base having a plurality of protrusions protruded to the outside from side faces to support a radiation detection panel; buffer members arranged in positions to face the protrusions; a frame for arranging the radiation detection panel, the base, and the buffer members inside; and a cover for closing an opening of the frame. The protrusions support the base into a predetermined position inside the frame through the buffer members and the cover. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a cassette for radiographic imaging, and more particularly to a cassette for radiographic imaging with improved shock resistance and vibration resistance characteristics.

  2. Description of the Related Art Conventionally, in a medical diagnosis field, an apparatus for obtaining a radiographic image by irradiating an object with radiation and detecting the radiation transmitted through the object has been used. Using a film / screen.

  This is because the phosphor that emits visible light when irradiated with radiation is adhered to both sides of the photosensitive film, the radiation that has passed through the object is converted into visible light by the phosphor, and this visible light is converted into a photosensitive film. By capturing and developing by chemical processing, the latent image formed on the photosensitive film is visualized to obtain a radiation image.

  In recent years, with the advance of digital technology, CR (Computed Radiography) systems capable of handling radiation images as digital data have been put into practical use.

  The CR cassette used in this system has a built-in phosphor plate on which a stimulable phosphor layer is formed so that radiation transmitted through the object can be absorbed by the stimulable phosphor layer and stored as radiation energy. it can.

  After imaging, the phosphor plate is scanned with excitation light by another device, and the radiation energy accumulated in the stimulable phosphor layer is emitted as stimulated emission light, and the emitted stimulated emission light is photoelectrically converted. Thus, an electric signal corresponding to the radiation dose can be obtained.

  Next, image processing is performed on this electric signal and the result is displayed on a display device such as a CRT, whereby a high-quality radiation image can be obtained.

  However, there is a further demand for facilitating photographing work, and an FPD (Flat Panel Detector) system has been developed in place of the above-described CR cassette due to the recent development of semiconductor manufacturing technology.

  The FPD cassette used in this FPD system has a built-in one in which a plurality of radiation detection elements are two-dimensionally arranged on a substrate, and outputs an electrical signal corresponding to the amount of radiation irradiated to the radiation detection elements. is there. If this FPD cassette is used, it is possible to obtain radiographic image data directly without scanning the excitation light and to emit the stimulated emission light. Therefore, it is possible to perform the photographing work more than when the CR cassette is used. It becomes possible to make it smooth.

  Although the FPD cassette was initially installed in the radiation room, in recent years, a portable type that is as easy to use as the CR cassette has been demanded in order to enable more rapid and wide range imaging.

  However, since the FPD cassette has a built-in substrate made of a fragile material such as glass, in order to actually carry and use it at medical sites, etc., it is resistant to shocks such as dropping and vibration during movement. The vibration resistance against was insufficient.

  For this reason, an FPD cassette has been developed in which a shock-absorbing material is provided between the substrate and the frame to improve vibration resistance and impact resistance.

  FIG. 8 is an explanatory diagram of a conventional FPD cassette.

  In the conventional FPD cassette 100, the frame 101 is sealed with a lid 102, and a metal base 105 is attached to the frame 101 via a spacer 104.

  On the base 105, a substrate 106 made of a glass plate, a photoelectric conversion element 107 formed in a two-dimensional array by a semiconductor process, and a fluorescent plate 108 in which a phosphor made of a metal compound is applied to a resin plate are laminated. An X-ray panel 109 is provided.

  A circuit board 110 on which electronic parts for processing photoelectrically converted electric signals are mounted on the lower surface of the base 105 is fixed to the base 105 through protrusions 111. The circuit board 110 and the photoelectric conversion element 107 are mounted on the base 105. They are connected by a flexible circuit board 112.

  The flexible circuit board 112 is provided with signal lines and control lines for reading an electrical signal from the photoelectric conversion element 107. A plurality of flexible circuit boards 112 are arranged on the outer periphery of the board 106. It passes through the side and is routed to the circuit board 110 disposed on the back surface of the base 105.

  The buffer material 114 having the protrusion 113 is disposed between the outer peripheral portion of the base 105 and each flexible circuit board. When the lid 102 is deformed, the protrusion 113 of the buffer material 114 is the side surface of the base 105. , And the deformation of the lid 102 is suppressed, and the safety against an impact from the side of the FPD cassette 100 can be further improved (see, for example, Patent Document 1).

JP 2001-346788 A

  The FPD cassette 100 described in Patent Document 1 includes a spacer 104 attached to a frame 101 that supports a base 105, and a cushioning material that is disposed on the outer periphery of the base 105 that protects the base 105 from impact and has a protrusion 113. 114 are provided as separate members.

  Since the spacer 104 and the buffer material 114 are provided as separate members, there is a problem that the thickness of the FPD cassette 100 in the X-ray incident direction is increased and the outer dimensions of the FPD cassette 100 are increased. .

  In addition, since the FPD cassette has begun to be used in a usage form of a portable CR cassette, it is desirable that the FPD cassette can also be used for a radiographic apparatus (Bucky) for the CR cassette.

  However, since the FPD cassette 100 needs to arrange electronic components such as the flexible circuit board 112 and the circuit board 110 inside the frame 101, the outer dimensions thereof are larger than those of the CR cassette. The FPD cassette 100 having a size larger than that of the CR cassette cannot be diverted to a CR cassette radiography apparatus (Bucky).

  The present invention has been made in view of the above-described problems, and protects a built-in member from damage caused by an impact or the like, and is compatible with a radiographic apparatus (bukky) for CR cassette and an FPD system. An object is to provide a usable cassette for radiographic imaging.

  The above object is achieved by the following invention.

1. A base having a plurality of protrusions protruding outward from the side surface and supporting the radiation detection panel;
A cushioning material disposed at a position facing the protrusion;
A frame in which the radiation detection panel, the base and the cushioning material are disposed;
A lid that closes the opening of the frame;
A cassette for radiographic imaging, wherein the projection supports the base at a predetermined position inside the frame via the cushioning material and the lid.

  2. The cassette for radiographic imaging according to 1 above, wherein the lid has a buffer material fitting portion into which the buffer material is fitted.

  3. The cassette for radiographic imaging according to 2 above, wherein the buffer material fitting portion is a recess provided in the lid.

  4). 4. The radiographic imaging cassette according to 2 or 3, wherein the cushioning material has a protrusion fitting portion into which the protrusion is fitted.

  5. 5. The radiographic imaging cassette according to 4 above, wherein the protrusion fitting portion is a recess provided in the cushioning material.

  6). The protrusion of the base is fitted to the protrusion fitting portion of the cushioning material, the cushioning material is fitted to the cushioning material fitting portion of the lid, and the lid is fixed to the frame. The radiographic imaging cassette according to 5 above, wherein the base is supported at a predetermined position inside the frame.

  7). The projection and the buffer material form a space between a side surface of the base and a side surface of the frame, and an electrical component is disposed in the space. A cassette for radiographic imaging as described in 1.

  8). 8. The radiographic imaging cassette according to claim 7, wherein the electrical component disposed in the space is disposed between the plurality of protrusions.

  9. The protrusion provided on one side surface of the base and the protrusion provided on the other side opposite to the one side surface are provided at positions symmetrical with respect to the base. The cassette for radiographic imaging as described in any one of 1 to 8 above.

  10. The protrusion provided on one side of the base and the protrusion provided on the other side opposite to the one side are not provided in a line-symmetric position on the base. The cassette for radiographic imaging of any one of said 1-8 characterized by the above-mentioned.

  11. 11. The radiographic imaging cassette according to any one of 1 to 10 above, wherein the cassette has the same external dimensions as a CR cassette conforming to ISO 4090: 2001 used in a computed radiography system.

  According to the invention described in 1 to 11 above, the built-in member is protected from damage caused by impact or the like, and is used for radiographic imaging that can be used interchangeably with a radiographic apparatus (Bucky) for CR cassette and FPD system. Can be provided.

1 is an external perspective view of a portable radiographic image cassette. FIG. It is a schematic sectional drawing of the X part of the radiation cassette shown in FIG. It is explanatory drawing which shows the relationship between the base 7, the processus | protrusion 7a, the shock absorbing material 10, the lid | cover 3, and the flame | frame 2. FIG. It is explanatory drawing of the attachment position of the processus | protrusion 7a and the shock absorbing material 10. FIG. It is explanatory drawing which shows the relationship between the base 7, the processus | protrusion 7a, the shock absorbing material 10, and the lid | cover 3. FIG. It is a block diagram which shows the electrical structure of a radiation cassette. It is explanatory drawing which shows the circuit structure of the pixel Gab and the output circuit 23-b. It is explanatory drawing of the conventional FPD cassette.

  Hereinafter, embodiments of the present invention will be described with reference to the drawings. However, the technical scope of the present invention is not limited by the description in the description of the embodiments.

  FIG. 1 is an external perspective view of a portable radiographic cassette.

  A portable radiographic imaging cassette 1 (hereinafter, referred to as a radiographic cassette 1) includes a cylindrical frame 2 having a rectangular cross section, and a pair of rod-shaped lids 3 that block openings at both ends of the frame 2. The lid 3 is fixed to the frame 2 with screws or the like. The alternate long and short dash line indicates a state in which the lid 3 is removed from the frame 2.

  And radiation enters from the direction of arrow Z.

  FIG. 2 is a schematic cross-sectional view of a portion X of the radiation cassette shown in FIG.

  The radiation cassette 1 includes a scintillator 5 that converts radiation into light inside the radiation cassette 1 (a space surrounded by the frame 2 and the lid 3), a glass substrate 6 on which TFTs to be described later are laminated, and a flexible substrate that is flexible. 8. An electric circuit 9 having various electric parts, a buffer material 10 made of an elastic body, and a base 7 for supporting the scintillator 5, the glass substrate 6, the electric circuit 9, and the like. The scintillator 5, the glass substrate 6 on which the TFTs are stacked, the base 7, and the electric circuit 9 are arranged in that order with respect to the arrow Z direction in which the radiation enters.

  Hereinafter, the space 4 surrounded by the frame 2 and the lid 3, which is inside the radiation cassette 1 described above, will be referred to as a cassette interior 4.

  A combination of the scintillator 5 and the glass substrate 6 is referred to as a radiation detection panel P.

  The frame 2 is made of a light material that transmits light, for example, a carbon fiber body, and protects a member disposed inside the cassette 4 from an impact or the like by its rigidity.

  The lid 3 has a bar shape with a rectangular cross section, and is not particularly limited in material. For example, the lid 3 is made of a light metal such as aluminum or a resin. The lid 3 is fixed to the frame 2 with screws or the like, thereby sealing the cassette interior 4 from the outside air.

  The scintillator 5 receives the radiation transmitted through the object to be photographed and converts it into fluorescence in the visible light region.

  The material (glass) is selected for the glass substrate 6 from the viewpoints of having no chemical action with the semiconductor element, enduring the temperature of the semiconductor process, dimensional stability, and the like. The glass substrate 6 has a large number of photodiodes (not shown) for converting the fluorescence corresponding to the object to be photographed converted by the scintillator 5 into an electric signal, and the electric signal obtained by the photodiode is converted into an image signal. TFTs (Thin Film Transistors) having a large number of switching elements (not shown) are stacked.

  The base 7 has a plate shape having high rigidity to support the radiation detection panel P (scintillator 5, glass substrate 6), flexible substrate 8, and electric circuit 9, and the material is a metal such as aluminum or aluminum. It is composed of an alloy or a resin plate having a honeycomb structure.

  Further, the base 7 has a plurality of protrusions 7a (broken lines) protruding outward from the side surfaces, and the protrusions 7a support the base 7 at a predetermined position inside the radiation cassette 1 via the cushioning material 10. Yes. Further, the buffer material 10 is disposed at a position facing the protrusion 7a.

  The shape of the protrusion 7a (broken line) of the base 7 is a prismatic shape, for example, a quadrangular prism shape. It may be cylindrical (cylindrical, elliptical).

  Further, the protrusion 7 a is formed integrally with the base 7. The protrusion 7a may be a separate member. In this case, the protrusion 7a is fixed to the base 7 with a screw or the like.

  The electric circuit 9 is provided with a battery (not shown) for supplying power to various circuits, a control element (not shown) for transmitting an image signal acquired by the TFT to an external device, and the like.

  The flexible substrate 8 connects the TFT of the glass substrate 6 and the electric circuit 9. The flexible substrate 8 is provided with signal lines and control lines for electrically connecting the TFT and the electric circuit 9, and a plurality of signal lines and control lines are connected to the outer periphery of the TFT. Each flexible substrate 8 passes through the side of the base 7 and between the protrusions 7 a and is routed to the electric circuit 9 disposed on the back surface of the base 7.

  Various electric circuits may be provided on the flexible substrate 8 itself. By doing so, the utilization efficiency of the space between the base 7 and the frame 2 or the space between the base 7 and the lid 3 is improved, and the electrical components mounted on the glass substrate 6 or the electric circuit 9 can be reduced. Become.

  The cushioning material 10 is an elastic body having a predetermined hardness to protect the member disposed in the cassette interior 4 from impact or the like. For example, urethane rubber or silicon rubber having a hardness of 30 to 50 degrees can be used. The cushioning material 10 has a projection fitting portion 10a into which the projection 7a is fitted. The projection 7a is fitted into the projection fitting portion 10a, so that the base is placed at a predetermined position inside the frame 2, that is, inside the cassette 4. 7 is arranged.

  Further, the protrusion fitting portion 10a is a recess provided in the cushioning material 10, and the sectional shape of the recess is the same as the sectional shape of the projection 7a so that the projection 7a can be fitted to the cushioning material 10.

  Then, the projection 7 a of the base 7 is fitted into the projection fitting portion 10 a of the cushioning material 10, the cushioning material 10 is fitted into the cushioning material fitting portion 3 a of the lid 3, and the lid 3 is fixed to the frame 2. Thus, the base 7 is supported at a predetermined position inside the frame 2.

  As described above, the cushioning material 10 is formed of an elastic body, and the base 7 is supported inside the frame 2 via the projection 7a, the cushioning material 10 and the lid 3, so that the impact from the frame 2 or the lid 3 can be achieved. A radiation cassette capable of absorbing the glass substrate 6, the scintillator 5, the electric circuit 9, and the like supported by the base 7 from impacts and the like, and capable of supporting the base 7 at a predetermined position inside the radiation cassette 1. Made possible.

  FIG. 3 is an explanatory diagram showing a relationship among the base 7, the protrusion 7 a, the cushioning material 10, the lid 3, and the frame 2.

  The lid 3 has a cushioning material fitting portion 3a in which the cushioning material 10 is fitted at a predetermined position of the lid 3. The cushioning material 10 is fitted into the cushioning material fitting portion 3a, and the cushioning material 10 has a protruding fit. The base 7 is disposed at a predetermined position inside the frame 2 by fitting the projection 7a to the joint portion 10a.

  The cushioning material fitting portion 3 a is a recess provided in the lid 3, and the sectional shape of the recess is the same as the sectional shape of the cushioning material 10. The predetermined position is a position where the scintillator 5, the glass substrate 6, the electric circuit 9, etc. supported by the base 7 when an impact occurs does not contact the frame 2 or the lid 3, and the arrow of the lid 3 facing the protrusion 7 a. It is the position in the y direction and the arrow z direction.

  Since the base 7 is supported by the cover 3 via the cushioning material 10 and the protrusions 7a, the support of the base 7 and the shock absorption to the internal components of the frame 2 can be achieved simultaneously without increasing the size of the frame 2.

  3A is a conceptual cross-sectional view of the radiation cassette 1 shown in FIG. 1 (with the upper surface of the frame 2 removed) as viewed from above, and FIG. 3B is a diagram of the radiation cassette 1 shown in FIG. It is QQ 'cross section conceptual diagram.

  In FIG. 3 (a), the radiation cassette 1 is used interchangeably with a CR cassette (not shown) conforming to ISO 4090: 2001 used in the Computed Radiography system, so that the outer dimensions and image area dimensions are different from those of the CR cassette. It is the same.

  Specifically, C1 and C2 are external dimensions of the radiation cassette 1, and are the same as the external dimensions of the CR cassette of the same size standard. B1 and B2 are external dimensions of the scintillator 5 or the glass substrate 6 [TFT (photodiode, etc.)], and are slightly larger than the external dimensions of the phosphor plate of the CR cassette of the same size standard. A1 and A2 are the image area dimensions of the radiation cassette 1 and are the same as the image area dimensions of the CR cassette of the same size standard.

  3 (a) and 3 (b), the protrusion 7a and the cushioning material 10 support the base 7 at a predetermined position inside the cassette 4 so that the space between the upper surface of the base 7 and the upper inner surface of the frame 2 can be reduced. The first space 4a is formed in the second space 4b, and the second space 4b (that is, the space 4b formed by the projection 7a and the cushioning material 10) is formed between the side surface of the base 7 and the inner side surface of the lid 3. .

  In addition, the radiation cassette 1 that is an FPD cassette used in the FPD system has a large number of necessary electrical components, and at least one of the first space 4a and the second space 4b is used in order to efficiently use the space. Place electrical parts on For example, scintillators 5, a glass substrate 6, and electrical components such as TFTs are arranged in the first space 4a, and members such as a plurality of flexible substrates 8 are arranged in the second space 4b.

  In addition, the electric component (flexible substrate 8) arrange | positioned in the 2nd space 4b is arrange | positioned between the some protrusion 7a, respectively.

  It should be noted that the positions and number of the protrusions 7a and the cushioning material 10 can be set as long as the members arranged in the cassette interior 4 can be protected from impacts in the directions of the arrows x, y, and z. Any number of members may be disposed as long as the member disposed in the cassette interior 4 can be supported at the position. FIG. 3 shows a case where two protrusions 7 a are provided on the other side surface opposite to the one side surface of the base 7.

  As described above, the electric parts can be arranged on the upper surface, the lower surface, and the side surface of the base 7 so that the size and the outer dimension of the radiation cassette 1 can be made the same size as the CR cassette. By making the size and external dimensions of the image area of the radiation cassette 1 the same as the CR cassette, the radiation cassette 1 is moved to various places where the CR system or the FPD system is installed and is compatible with the CR cassette. It was also possible to use it.

  FIG. 4 is an explanatory diagram of the attachment positions of the protrusions 7a and the cushioning material 10.

  4A shows a case where the protrusion and the buffer material are provided in a line-symmetric position with respect to the base, and FIG. 4B shows a case where the protrusion and the buffer material are line-symmetric with respect to the base. The case where it is not provided in the position is shown.

  In FIG. 4A, the protrusion 71 a provided on one side surface 71 of the base 7 and the protrusion 72 a provided on the side surface 72 opposite to the one side surface are in a line-symmetrical position on the base 7. Is provided.

  The number of protrusions may be one or two or more per side if space permits, but preferably two or three. In the figure, an example in which two protrusions are arranged on each side surface is shown.

  In FIG. 4 (b), the protrusion 71 a provided on one side surface 71 of the base 7 and the protrusion 72 a provided on the side surface 72 opposite to the one side surface are in a line-symmetrical position on the base 7. It is not provided (it is provided at an asymmetrical position).

  The number of protrusions may be the same number (not shown) on both side surfaces or different numbers as shown. However, even in the case of the same number, unlike FIG. The figure shows an example in which two protrusions are arranged on one side and one protrusion is arranged on the other side.

  FIG. 5 is an explanatory diagram showing the relationship between the base 7, the protrusion 7 a, the cushioning material 10, and the lid 3.

  5 is a view seen from the same direction as FIG.

  The lid 3 is provided with a buffer material fitting portion 3a. The cushioning material fitting portion 3a is a recess having the same shape and size as the cross-sectional shape of the cushioning material 10, and the cushioning material 10 is not easily detached from the cushioning material fitting portion 3a due to its elasticity, and the cassette interior 4 can be removed from the outside air. It fits in the buffer material fitting part 3a to such an extent that it can be sealed.

  The lid 3 has a stepped portion (no part number) with which the frame 2 is fitted. By fitting the frame 2 into the stepped portion, the lid 3 is attached to the frame 2 with the arrows x, y, z described above. Positioned and fixed in direction.

  Further, the cushioning material 10 is provided with a protrusion fitting portion 10a. The protrusion fitting portion 10 a is a recess having the same shape and size as the cross-sectional shape of the protrusion 7 a and is fitted to such an extent that the protrusion 7 a is in close contact with the shock absorbing material 10 due to the elasticity of the shock absorbing material 10.

  The protrusion 7 a is fitted to the cushioning material 10 so that the base 7 is positioned with respect to the lid 3, and it is possible to protect the members arranged in the cassette 4 from the impact.

  In the drawing, a gap is shown between the cushioning material fitting portion 3a and the cushioning material 10 and between the projection fitting portion 10a and the projection 7a so that the respective relations can be clearly understood. Further, the cushioning material fitting portion 3a and the cushioning material 10, and the projection fitting portion 10a and the projection 7a are in close contact with each other due to the elasticity of the cushioning material 10, and there is no gap.

  Further, in the figure, the form in which the cushioning material 10 protrudes from the inner surface 3C of the lid 3 is shown. However, if the base 7 can be supported by the lid 3 via the cushioning material 10 and the projection 7a, the cushioning material 10 and the inner surface 3C of the lid 3 are cushioned. The end surface 10 </ b> C of the material 10 may be located on the same plane, and the end surface 10 </ b> C of the cushioning material 10 may be retracted from the inner surface 3 </ b> C of the lid 3.

  As described above, the mode in which the cushioning material fitting portion 3a is retracted from the inner surface 3C of the lid 3 has been described. However, the convex portion protruding from the inner surface 3C of the lid 3 toward the base 7 side at the position facing the protrusion 7a of the base 7. (Not shown) may be provided, and the cushioning material fitting portion 3a may be provided on the convex portion.

  As described above, the cushioning material 10 is formed of an elastic body, and the base 7 is supported inside the frame 2 via the protrusions 7a, the cushioning material 10, and the lid 3, so that the impact from the frame 2 or the lid 3 can be achieved. The glass substrate 6, the scintillator 5, the electric circuit 9, and the like supported by the base 7 can be protected from impacts and the like, and the base 7 (the glass substrate 6, the scintillator 5 is placed at a predetermined position inside the radiation cassette 1. The radiation cassette capable of supporting the electric circuit 9) can be provided.

  Furthermore, by making it possible to provide the arrangement position of the protrusion 7a with respect to the base 7 at a line-symmetrical or non-line-symmetrical position, the degree of freedom in designing the glass substrate and the FTF can be increased. The dimensions and external dimensions could be made the same as the CR cassette.

  As a result, the glass substrate 6, scintillator 5, electric circuit 9, etc. can be protected from impact and the like, and a radiation cassette that can be used interchangeably with a CR cassette radiography apparatus (buccy) and FPD system can be provided.

  One of the objects of the present invention is to protect the substrate (glass) of the glass substrate itself, TFTs laminated on the glass substrate, circuit components of the electric circuit 9 and the like from impacts, etc. explain.

  FIG. 6 is a block diagram showing an electrical configuration of the radiation cassette.

  The radiation cassette 1 includes a plurality of radiation detection elements G (pixels G11 to Gmn), a vertical scanning circuit 22 provided on the flexible substrate 8 or the electric circuit 9, an output circuit 23 (23-1 to 23-n), A multiplexer 24, an A / D conversion circuit 25, and a timing generator 26 are provided.

  The pixels G11 to Gmn are two-dimensionally arranged on the TFT (shown in FIG. 2). The DC voltage VDD is applied from the power supply line 27 to detect radiation and convert it into an electrical signal.

  The vertical scanning circuit 22 provided on the flexible substrate 8 or the electric circuit 9 applies the signals φV1 to φVm from the drive lines 28-1 to 28-m and outputs the pixels G11 to Gmn in the vertical direction when outputting electric signals. . The output circuits 23-1 to 23-n read and hold the electric signals output from the pixels G11 to Gmn for each row by the signal readout lines 29-1 to 29-n, and send them from the reset line 30 of the timing generator 26. Is reset by a reset signal φRST. Then, the multiplexer 24 converts the electric signals held by the output circuits 23-1 to 23-n into serial electric signals for each column. The A / D conversion circuit 25 converts the electrical signal supplied from the multiplexer 24 into digital data. The timing generator 26 designates the operation timing of the vertical scanning circuit 22, the output circuits 23-1 to 23-n, and the multiplexer 24b / D conversion circuit 25.

  Hereinafter, the configurations of the output circuits 23-1 to 23-n and the pixels G11 to Gmn will be described as representative of the pixel Gab in the a row and the b column and the output circuit 23-b in the b column.

  FIG. 7 is a diagram illustrating a circuit configuration of the pixel Gab and the output circuit 23-b.

  The pixel Gab includes a photodiode 31 and a switching element 32, and the output circuit 23-b includes a so-called charge sensing amplifier including an operational amplifier 231 and a capacitor 232.

  Fluorescence in the visible light region corresponding to the object to be photographed converted by the scintillator 5 enters the photodiode 31. The photodiode 31 accumulates charges in the anode in response to incident light, and the switching element 32 charges and discharges the charges accumulated in the anode.

  The charge sensing amplifier is a readout circuit having an integration function by holding the charge accumulated in the anode of the photodiode 31 in the capacitor 232, and even if the output, that is, the electric signal is read out unless the capacitor 232 is reset. State is preserved. Then, ON / OFF of the switch 233 is controlled by a signal φRST given from the timing generator 26 through the reset line 30.

  The operation of the pixel Gab and the output circuit 23-b will be described below.

  First, in order to perform the reset operation of the pixel Gab and the output circuit 23-b, the signal φRST is given from the timing generator 26, the switch 233 of the output circuit 23-b is turned on, and the charge accumulated in the capacitor 232 is discharged. . At the same time, the signals φV1 to φVm are given from the vertical scanning circuit 22, and the switching element 32 of the pixel Gab is turned on to discharge the charge of the photodiode 31.

  When the imaging operation is performed, on the other hand, the signal φVa is turned off, the switching element 32 is turned off, and the electric charge obtained by photoelectric conversion by the photodiode 31 is accumulated in the anode of the photodiode 31.

  On the other hand, the signal φRST of the output circuit 23-b is turned off, the switch 233 is turned off, and the electric charge accumulated in the anode of the photodiode 31 is accumulated in the capacitor 232 as an electric signal. As a result, the voltage value of the output terminal of the operational amplifier 231 is changed, and the voltage value of the output terminal of the operational amplifier 231 is applied to the multiplexer 24 through the signal readout line 29-b.

  The multiplexer 24 converts the obtained voltage value into a serial electric signal and transmits it to the A / D conversion circuit 25. The A / D conversion circuit 25 converts this electric signal into digital data. In this way, radiation image data is created by the radiation image capturing apparatus 1.

  In the radiation cassette 1 described above, the radiation transmitted through the object is converted into visible light by the scintillator 5 according to the radiation intensity, and the visible light is converted into an electrical signal by the photodiode and the switching element. The image signal converted by the photodiode or the like is transmitted to an external device as radiographic image data via the electric circuit 9 or the like, and the radiographic image is provided to a medical staff by an external device (for example, a display device such as a CRT). The

  The transmission of the radiation image data to the external device may be performed by providing a wired communication means in the electric circuit 9 or by providing a wireless communication means in the electric circuit 9.

  As described above, it is possible to provide medical personnel with radiation image data that has passed through an object as a radiation image, and a radiation cassette that can be used in a compatible manner with a CR imaging radiation imaging apparatus (Bucky) and an FPD system. I was able to provide it.

  Hereinafter, an example of the assembly of the radiation cassette will be described with reference to FIGS.

  1. A glass substrate 6, a scintillator 5, an electric circuit 9, a flexible substrate 8, and the like are assembled to the base 7. Then, the cushioning material 10 is assembled to the cushioning material fitting portion 3a of the lid 3, and the assembled lid 3 is fixed to the frame 2 with screws or the like.

  2. The base 7 assembled in the previous step is inserted into the frame 2 so that the protrusions 7a are fitted into the cushioning material 10 of one lid 3.

  3. The other lid 3 is fixed to the frame 2 with screws or the like so that the cushioning material 10 of the other lid 3 fits into the protrusion 7a.

  As described above, the cushioning material 10 can be assembled to the lid 3 in advance, and the assembly of the radiation cassette can be completed in three steps. As a result, the assembly can be easily performed. Can be provided.

DESCRIPTION OF SYMBOLS 1 Radiation cassette 2 Frame 3 Lid 3a Buffer material fitting part 5 Scintillator 6 Glass substrate 7 Base 7a Protrusion 8 Flexible substrate 9 Electric circuit 10 Buffer material 10a Projection fitting part 31 Photodiode 32 Switching element

Claims (11)

A base having a plurality of protrusions protruding outward from the side surface and supporting the radiation detection panel;
A cushioning material disposed at a position facing the protrusion;
A frame in which the radiation detection panel, the base and the cushioning material are disposed;
A lid that closes the opening of the frame;
A cassette for radiographic imaging, wherein the projection supports the base at a predetermined position inside the frame via the cushioning material and the lid.   The radiographic imaging cassette according to claim 1, wherein the lid includes a buffer material fitting portion into which the buffer material is fitted.   The cassette for radiographic imaging according to claim 2, wherein the cushioning material fitting portion is a concave portion provided in the lid.   The cassette for radiographic imaging according to claim 2, wherein the cushioning material has a projection fitting portion into which the projection is fitted.   The cassette for radiographic imaging according to claim 4, wherein the protrusion fitting portion is a recess provided in the cushioning material.   The protrusion of the base is fitted to the protrusion fitting portion of the cushioning material, the cushioning material is fitted to the cushioning material fitting portion of the lid, and the lid is fixed to the frame. The radiographic imaging cassette according to claim 5, wherein the base is supported at a predetermined position inside the frame.   The projection and the buffer material form a space between a side surface of the base and a side surface of the frame, and an electrical component is disposed in the space. The cassette for radiographic imaging as described in the item.   The radiographic imaging cassette according to claim 7, wherein the electrical component disposed in the space is disposed between the plurality of protrusions.   The protrusion provided on one side surface of the base and the protrusion provided on the other side opposite to the one side surface are provided at positions symmetrical with respect to the base. The cassette for radiographic imaging of any one of Claims 1-8.   The protrusion provided on one side of the base and the protrusion provided on the other side opposite to the one side are not provided in a line-symmetric position on the base. The cassette for radiographic imaging of any one of Claims 1-8 characterized by the above-mentioned.   11. The radiographic imaging cassette according to claim 1, wherein the cassette for radiographic imaging according to claim 1 has the same external dimensions as a CR cassette conforming to ISO 4090: 2001 used in a Computed Radiography system.

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